Old Users Guide:Beam modelling
Photon beam : LINAC
A realistic photon beam in a multilayer phantom can be modelled using GATE. The phantom is irradiated with a photon beam, originating from a uniform point source at a certain distance from the phantom surface and collimated at the surface of the phantom using. The energy spectrum of the point source is modelled using the configurations of a VARIAN Clinac for example. The depth dose distribution was calculated along the central axis with a 1D . The production threshold can be set to different values in the world and in the phantom for electrons, positrons and photons.
Hadron therapy application
As an example of a hadron therapy application, we simulate a 12C scanning pencil beam irradiation of an artificial spherical target inside a patient CT image. The treatment plan comprised different pencil beams. Figure 3 illustrates the dose deposition measured using GATE.
In-beam PET modelling
GATE is able to jointly model radiation therapy and emission tomography in order to monitor the deposited dose for a 12C treatment using PET imaging as shown in Figure 4. It models the Carbon beam, the nuclear fragmentation, the β+ emitters, back to back photon and dose monitoring!
A 4D CT patient scan was used to define the numerical phantom. A three beam treatment plan was modelled with a total production of 3 beams of 109 12C ions. Each beam was composed of 195 independent spots with 42 different incident energies between 175 and 230 MeV/u. All hadronic and electromagnetic processes were included in the simulation. Positron range and annihilation photon pair acollinearity were taken into account. A model of the Siemens HR+ PET system was used to simulate a 20 min static acquisition starting immediately after the irradiation. PET data were normalized, corrected for attenuation using an attenuation map derived from the CT, and reconstructed using 3D back projection. The simulation was performed in less than 24 h on a cluster of 1000 Intel Nehalem 2.93 GHz CPUs. Figure 5 shows the reconstructed PET images. It suggests that the 11C activity distribution contains most information regarding the location of the Spread Out Bragg Peak (SOBP), while the 15O activity might be relevant to derive information about the dose to normal tissues.